EP3285697B1 - Procédé pour contrôler l'amortissement de la phase d'appui d'une prothèse du genou - Google Patents

Procédé pour contrôler l'amortissement de la phase d'appui d'une prothèse du genou Download PDF

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EP3285697B1
EP3285697B1 EP16716594.3A EP16716594A EP3285697B1 EP 3285697 B1 EP3285697 B1 EP 3285697B1 EP 16716594 A EP16716594 A EP 16716594A EP 3285697 B1 EP3285697 B1 EP 3285697B1
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Prior art keywords
flexion
damping
knee angle
max
maximum
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German (de)
English (en)
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EP3285697A1 (fr
Inventor
Dirk Seifert
Sven Zarling
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Otto Bock Healthcare Products GmbH
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Otto Bock Healthcare Products GmbH
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/60—Artificial legs or feet or parts thereof
    • A61F2/64—Knee joints
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/70—Operating or control means electrical
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A—HUMAN NECESSITIES
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    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A61F2002/6818—Operating or control means for braking
    • A—HUMAN NECESSITIES
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    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/70—Operating or control means electrical
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/70—Operating or control means electrical
    • A61F2002/704—Operating or control means electrical computer-controlled, e.g. robotic control
    • A—HUMAN NECESSITIES
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    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/76—Means for assembling, fitting or testing prostheses, e.g. for measuring or balancing, e.g. alignment means
    • A61F2002/7615—Measuring means
    • A61F2002/7625—Measuring means for measuring angular position
    • A—HUMAN NECESSITIES
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/76—Means for assembling, fitting or testing prostheses, e.g. for measuring or balancing, e.g. alignment means
    • A61F2002/7615—Measuring means
    • A61F2002/7635—Measuring means for measuring force, pressure or mechanical tension
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
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    • A61F2002/764—Measuring means for measuring acceleration

Definitions

  • the invention relates to a method for controlling the stance phase damping of an artificial knee joint with a top and a bottom, which are pivotally mounted together about a pivot axis, and a resistance unit which is disposed between the top and the bottom and having an adjusting device via which the damping resistance can be changed, with a control unit which is coupled to the adjusting device and which is connected to at least one sensor, wherein the adjustment is carried out on the basis of sensor data.
  • Knee joints for orthoses, exoskeletons or prostheses have an upper part with an upper connection part and a lower part with a lower connection part, which are connected to one another in an articulated manner.
  • On the upper connection part receptacles are usually arranged for a thigh stump or a thigh rail, while at the lower connection part a lower leg tube or a lower leg rail are arranged.
  • the upper part and the lower part are pivotally connected to each other by a uniaxial joint.
  • a resistance device which provides a flexion resistance and an extension resistance.
  • About the flexion resistance is set how easy the lower part can swing in relation to the upper part with an applied force to the rear.
  • the extension resistance slows the forward movement of the lower part and forms, among other things, a stretch stop.
  • the DE 10 2006 021 802 A1 describes a control of a passive prosthetic knee joint with adjustable damping in the direction of flexion for adapting a prosthesis device with upper-side connecting means and a connecting element to an artificial foot.
  • the adaptation is made to the stair climbing, whereby a low-torque lifting of the prosthetic foot is detected and the flexion damping is lowered in a lifting phase to below a level that is suitable for in-plane walking.
  • the flexion damping can be increased depending on the change in the knee angle and depending on the force acting on the lower leg axial force.
  • the DE 10 2009 052 887 A1 describes inter alia a method for controlling an orthotic or prosthetic joint with a resistance device and sensors, wherein status information is provided via sensors during the use of the joint.
  • the sensors detect moments or forces, wherein the sensor data of at least two of the determined variables are linked together by a mathematical operation and thereby an auxiliary variable is calculated, which is used as the basis for the control of the bending and / or yield resistance.
  • the DE 10 2012 013 141 A1 relates to a method for controlling an orthotic or prosthetic knee joint device with a drive device for acting on the knee joint device with a moment. To assist the patient, it is provided that prior to the flexion or extension of the knee joint device, the latter is subjected to a bending moment and a stretching moment which is below the level, which leads to a deflection or extension.
  • the sensor data are quantitatively evaluated, that is to say that certain limit values are generally specified, upon reaching or not reaching which the actuator is activated or deactivated, so that the resistance device has an increased or reduced flexion or extension resistance.
  • Patients can use prostheses, exoskeletons or orthoses in different environments. You can go down stairs, down ramps, or go at different speeds in the plane. Furthermore, loads can be carried, which also affects the behavior of the prosthesis or orthosis. In particular, after completion of the swing phase, so after placing the supplied leg, when the body weight is transferred to the supplied leg, there is often a need for patients for increased safety. Too high an initial flexion damping, ie an attenuation that counteracts an articulation of the artificial knee joint, would however lead to a shock-like load in the hip joint, which would result in a reduction of the wearing comfort and the acceptance of the prosthesis or orthosis.
  • the object of the present invention is to provide a method for controlling an artificial knee joint, in particular the change in damping within an artificial knee joint, with which an adaptation to different gait situations and a comfortable gait behavior with simultaneous maximum safety can be achieved.
  • the method for controlling the stance phase damping of an artificial knee joint having a top and a bottom pivotally mounted together about a pivot axis and a resistance unit interposed between the upper part and the lower part is arranged and having an adjusting device, via which the damping resistor can be changed, with a control unit which is coupled to the adjusting device and which is connected to at least one sensor, wherein the adjustment is carried out on the basis of sensor data, sees during the stance phase bending to the terminal stance phase, the knee angle is detected via the at least one sensor and the flexion damping is raised to a level above an initial flexion damping until avoidance of further bending when a defined maximum knee angle is reached.
  • the damping resistance essentially the flexion resistance
  • the damping resistance is set at a level suitable to provide sufficient cushioning in a heel contact.
  • the level is then the level of an initial inflection damping.
  • the knee angle increases, as a floor reaction force is impulsively built up by the heel contact and a torque about the pivot axis is caused due to the introduction of force together with a forward movement of the body.
  • An unoccupied leg would cushion the heel strike due to muscle contractions, for a supplied leg this is caused by the resistance unit with the initial flexion damping.
  • a flexion angle or knee angle of about 5 ° is achieved.
  • the stress response the load on the leg increases with body weight, resulting in further bowing or destabilization of the knee joint.
  • An unaided leg will interfere with further involvement by tensing the leg extensor muscles.
  • the flexion damping is raised to a level above the initial flexion damping, which is sufficient to prevent further flexing upon reaching a defined maximum knee angle.
  • the maximum achievable knee angle is determined in advance, while walking on ramps or in the plane, the maximum knee angle is in a range between 7 ° and 12 °.
  • the change in the flexion damping is thus to the extent that the flexion loss is monitored with increasing knee angle, with a maximum extended position has the knee angle 0 °, whether and how the knee angle increases. If the knee angle approaches the specified maximum knee angle, the flexion damping is increased, preferably one Progressive increase instead, ie initially a slow increase of the flexion damping, and then just before reaching the set maximum knee angle to increase the flexion damping so that a further inflection can not take place, thus a flexion stop is effected.
  • the resistance unit which may be configured, for example, as a hydraulic, pneumatic, electrical or mechanical resistance unit or brake is blocked. In hydraulic or pneumatic resistance units overflow channels are closed, so that no medium can flow from an extension chamber in a flexion chamber.
  • the method is intended to control both prostheses and orthoses and exoskeletons. If the following is spoken of orthoses, the statements also apply to the special form of the orthosis in the form of an exoskeleton.
  • the sensor or sensors record the measurements over the entire stance phase, as from the moment of the first contact of the foot or foot with the ground, the initial ground contact, heel strike or heel strike, to the terminal stance phase, in which a full extension of the knee joint and the knee joint is held in an extended position via a resistance to a dorsal extension and the position of the force vector in front of the knee axis.
  • the terminal stance phase in the so-called pre-swing phase, the swing phase is prepared, in a healthy leg passive flexion of the knee joint occurs, but the toes are not yet lifted off the ground.
  • a development of the invention provides that the flexion damping is maintained at the level that is present when the maximum knee angle is reached. As a result, an increased level of security is provided so that the artificial knee joint does not collapse in the further course of the gait.
  • the knee angle follows after a relative maximum, ie an extension that extends to the termial stance phase. In this phase, the knee angle decreases to a full extension. Maintaining the flexion loss at the level of the maximum knee angle during the stress response thus enhances safety without negatively affecting in-plane walking.
  • the flexion damping can be kept constant during the initial heel contact and increased depending on the load.
  • the elevation advantageously takes place only after reaching the so-called stress response, a phase of the aisle in which the foot has complete contact with the ground and the force vector moves behind the knee axis after the initial heel strike, causing knee flexion and activating the anterior femoral muscle in a healthy leg, to decelerate the bow.
  • the flexion damping is increased as a function of the load, the flexion damping according to the heel strike, with a large load more increased than with a low load.
  • a development of the invention provides that a forward rotation of the lower part, ie of the lower leg tube in a prosthesis or in an orthosis of a lower leg splint, is detected around a distal pivot point, preferably sensory detected. Movement of the lower leg around the ankle joint or around a fictitious pivot point in the floor area is detected or detected in order to be able to draw conclusions about the further movement behavior. With continued forward rotation after reaching the maximum knee angle, flexion loss can then be reduced to allow for a sufficiently easy knee flexion during the terminal stance phase or the fore phase so that toe separation can easily occur.
  • the flexion damping can be reduced after exceeding a predetermined range of forward rotation and / or at a decreasing knee angle.
  • the range of forward rotation may be a fixed one Include angular range about which the base must make a forward turn about a distal pivot point. For example, if 5 ° to 10 ° forward rotation is detected, control assumes that further forward movement has occurred either when walking in the plane or when going down ramps and / or stairs alternately, and a reduction in flexion damping is necessary.
  • the reduction in flexion damping based on monitoring a fixed range of forward rotation may be employed separately or in combination with the detection of a decreasing knee angle.
  • the flexion damping may be reduced to a value greater than or equal to the initial standstill phase loss after setting the maximum flexion damping of the initial stance phase. As a result, for example, when going down ramps or stairs, an increased level of security against unwanted bowing is also provided.
  • a development of the invention provides that after reaching a fixed maximum knee angle and a forward rotation of the lower part, the flexion damping is reduced. If, during walking, in particular when descending ramps or inclined planes, the maximum knee angle is reached or determined for the patient, and, moreover, a forward rotation of the lower part, which is detected for example by an inertial angle sensor or an ankle joint angle sensor, according to the invention Flexion resistance is reduced to provide a further bending of the knee joint and thus a smooth walking and a natural gait.
  • the maximum knee angle can be selected and set from a range between 7 ° and 12 ° or between 11 ° and 9 °, a common value for maximum knee angle is 10 °. This is about half of that knee angle that is reached by an unproven leg as an intervention during the stress response.
  • the maximum knee angle can also be based on statistical analysis detected knee angle are set for walking in the plane, the statistical evaluations in the control unit of the artificial knee joint can be performed. This makes it possible that the maximum knee angle for the user of the artificial knee joint is individually determined.
  • the method is suitable for controlling the stance phase damping, in particular when walking in the plane as well as when going downhill, the special situation of a staircase departure requires a different control.
  • the resistance unit can be designed, for example, as an actuator, for example as a hydraulic, pneumatic, magnetorheological, magnetic, electrical, mechanical or electromagnetic resistance unit.
  • an actuator for example as a hydraulic, pneumatic, magnetorheological, magnetic, electrical, mechanical or electromagnetic resistance unit.
  • overflow channels are closed, so that these transfer channels no medium can flow from an extension chamber in a flexion chamber. In this way, the flow of the medium between the extension chamber and the flexion chamber may possibly also be completely prevented.
  • mechanical resistance devices for example, the friction is increased so far that no further flexion can take place. The same applies to electrically actuated resistor units.
  • Actuators which both actively introduce energy into the system and, conversely, extract energy from the system and thus act as a resistance unit.
  • Actuators can be designed, for example, as electric motors, hydraulic or pneumatic pumps or piezoelectric elements.
  • FIG. 1 is a schematic representation of a prosthetic leg with an upper part 1 shown, on which a thigh shaft 10 is fixed for receiving a thigh stump.
  • a lower part 2 is pivotally arranged in the form of a lower leg part.
  • the lower part 2 is pivotally mounted on the upper part 1 about a pivot axis 4.
  • the lower part 2 has a lower leg tube 5, at the distal end of a prosthetic foot 3 is fixed, in which a means for determining the effective axial force on the lower leg tube 5 and the ankle moment, which is effective around the attachment point of the prosthetic foot 3 on the lower leg tube 5 can be accommodated.
  • a resistance device 6, which may be formed for example as a damper or actuator, is arranged, which is supported between the upper part 1 and the lower part 2, to provide an adjustable extension resistance and flexion resistance.
  • the resistance device 6 is associated with an adjusting device 7, for example a motor, a magnet or another actuator, via which the respective resistor R within the resistance device 6 can be changed.
  • the resistance device 6 is designed as a hydraulic damper or pneumatic damper, the respective flow cross section of an overflow channel can be increased or reduced via the adjusting device 7.
  • the flow resistance can be varied in a different manner. This can be done for example by opening or closing valves or changes in viscosities or magnetorheological properties.
  • the resistance device is designed as an electric motor in generator operation, an increase or decrease in the respective resistances to a flexion or extension can be set by changing the electrical resistance.
  • a control device 8 is assigned to the lower part 2, in particular mounted in a lower leg cover, via which a corresponding activation or deactivation signal is output to the adjusting device 7.
  • the adjusting device 7 is activated or deactivated on the basis of sensor data, the sensor data are supplied by one or more sensors 9, which are arranged on the artificial knee joint. These can be angle sensors, acceleration sensors and / or force sensors.
  • the sensors 9 are connected to the control device 8, for example by cable or via a wireless transmitting device.
  • the sensor 9 is formed, inter alia, as a knee angle sensor.
  • the sensors 9 are used to monitor the entire step cycle from the heel strike (Heel Strike) to the subsequent Heel Strike HS, thus also the entire swing phase with the swing phase extension and the swing phase flexion.
  • FIG. 2 is plotted on a graph over time, the knee angle ⁇ and the flexion damping F D.
  • the knee angle ⁇ is sketched for two walking situations from the beginning of the stance phase, ie from Heel Strike HS, to the terminal stance phase.
  • the lower curve ⁇ P shows the knee angle curve for walking in the plane
  • the upper curve ⁇ S shows the knee angle curve for the descent on a ramp or staircase, which is the representation of the supplied leg in an alternating walking.
  • a safe damping behavior of the pharyngeal bowing to provide the damping resistance F D or flexion resistance is initially set to an initial damping level F DI , which allows an articulation of the artificial knee joint during initial ground contact, the attenuation attenuates and decelerates to prevent collapse of the artificial knee joint.
  • This initial flexion damping F DI is initially maintained constant until the knee angle ⁇ has reached a threshold value.
  • the threshold value is about 30% of the specified, permitted or permissible maximum knee angle ⁇ max , the increase of the flexion damping F D begins almost immediately after the heel contact.
  • the threshold value may also be at a larger knee angle, for example at 50% or 70% of the specified, permitted or admissible maximum knee angle ⁇ max .
  • the flexion damping F D is increased in order to brake the further flexion of the knee joint and block ⁇ max when the maximum knee angle is reached.
  • the flexion damping is increased progressively, but it can also be increased degressive or linear.
  • the flexion damping F D is on reaching the maximum knee angle ⁇ max on the maximum flexion damping value F Dmax , in which a further flexion is no longer possible.
  • This resistance value Dmax F is maintained for a specified period .DELTA.T, it forms a plateau Dp of the maximum Flexionswiderstandes F Dmax, while this time, no flexion of the artificial knee joint is possible.
  • the period .DELTA.T for which this level F Dmax is maintained, is detected either via a timing switch or via the detection of a forward rotation ⁇ of the lower part 2, for example of the lower leg tube 5 or a pivot around the ankle joint of the prosthetic foot 3. If a further forward rotation by the angle ⁇ takes place, which can be detected by acceleration sensors, angle sensors and / or inertial angle sensors, the user of the artificial knee joint moves further forward. As a possible angular range for a further forward rotation ⁇ 5 ° to 10 ° pivot angle can be assumed. After reaching the limit value for the further forward rotation or the time lapse, the flexion damping F Dmax is reduced.
  • the reduction takes place in the illustrated embodiment degressive, so that First, a rapid drop in flexion damping is effected, for example, to allow a further inflection during ramping, as it shows the course of the curve ⁇ S.
  • Other gradients of attenuation reduction can be adjusted, for example, progressive or linear.
  • In the plateau region with the resistance plateau Dp during the time ⁇ T no further flexion movement of the artificial knee joint takes place. Only after lowering of the flexion resistance F D to a level below the maximum flexion resistance F Dmax , in the embodiment shown above a level of the initial flexion damping F DI in the region of the lowering curve F DS , is an increasing deflection possible.
  • the advantage of this control lies in the high degree of safety, which is based on an initial, always limited knee flexion to the maximum knee angle ⁇ max , without limiting the range of motion or the functionality during the further course of motion. If the maximum knee angle ⁇ max is reached and the leg rotates further forward, without causing a knee extension, as shown in the curve ⁇ S , the flexion damping F D is continuously up to a high attenuation, possibly down to the initial flexion damping F DI reduced. Thus, when going down ramps or stairs without compromising security, it is ensured that undisturbed further movement can take place.

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  • Health & Medical Sciences (AREA)
  • Transplantation (AREA)
  • Veterinary Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Vascular Medicine (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Biomedical Technology (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Epidemiology (AREA)
  • Pain & Pain Management (AREA)
  • Physical Education & Sports Medicine (AREA)
  • Rehabilitation Therapy (AREA)
  • Prostheses (AREA)

Claims (10)

  1. Procédé pour commander l'amortissement en phase debout d'une articulation artificielle de genou, comportant une partie supérieure (1) et une partie inférieure (2) qui sont fixées l'une à l'autre de façon mobile en basculement autour d'un axe de basculement (4), et une unité de résistance (6) qui est agencée entre la partie supérieure (1) et la partie inférieure (2) et qui présente un moyen de réglage (7) permettant de modifier la résistance d'amortissement (FD), comportant une unité de commande (8) qui est couplée au moyen de réglage (7) et qui est connectée au moins à un capteur (9), le réglage ayant lieu en se basant sur des données de capteur,
    caractérisé en ce que
    pendant la flexion en phase debout jusqu'à la phase debout terminale, l'angle (α) du genou est détecté par ledit au moins un capteur (9) et l'amortissement de flexion (FD) est augmenté à un niveau (FDmax) au-dessus d'un amortissement de flexion initial (FDI) jusqu'à éviter une poursuite de la flexion lorsqu'un angle maximal fixé (αmax) du genou est atteint.
  2. Procédé selon la revendication 1,
    caractérisé en ce que
    l'amortissement de flexion (FD) est maintenu au niveau (FDmax) lorsque l'angle maximal (αmax) du genou est atteint.
  3. Procédé selon la revendication 1 ou 2,
    caractérisé en ce que
    l'amortissement de flexion (FD) est maintenu constant pendant le contact initial du talon, et l'amortissement de flexion (FD) est augmenté en fonction de la charge.
  4. Procédé selon l'une des revendications précédentes,
    caractérisé en ce que
    une rotation vers l'avant de la partie inférieure (2) autour d'un point de rotation distal est détectée et lors d'une poursuite de la rotation vers l'avant, une fois que l'angle maximal (αmax) du genou est atteint, l'amortissement de flexion (FD) est réduit.
  5. Procédé selon l'une des revendications précédentes,
    caractérisé en ce que
    l'amortissement de flexion (FD) est réduit après dépassement d'une zone fixée de la rotation vers l'avant et/ou lors d'une réduction de l'angle (α) du genou.
  6. Procédé selon la revendication 4 ou 5,
    caractérisé en ce que
    l'amortissement de flexion (FD) est réduit à une valeur supérieure ou égale à l'amortissement de flexion initial (FDI) en phase debout.
  7. Procédé selon l'une des revendications précédentes,
    caractérisé en ce que
    l'amortissement de flexion (FD) est réduit une fois que l'angle maximal fixé (α) du genou est atteint et après une rotation relative vers l'avant de la partie inférieure (2).
  8. Procédé selon l'une des revendications précédentes,
    caractérisé en ce que
    l'angle maximal (αmax) du genou est choisi et fixé dans une plage entre 7° et 12° ou dans une plage entre 9° et 11°.
  9. Procédé selon l'une des revendications précédentes,
    caractérisé en ce que
    l'angle maximal (αmax) du genou est fixé en se basant sur des évaluations statistiques d'angles de genou (α) saisis pour la marche dans le plan.
  10. Procédé selon l'une des revendications précédentes,
    caractérisé en ce que
    l'angle maximal (αmax) du genou peut être fixé individuellement pour l'utilisateur respectif de l'articulation artificielle de genou.
EP16716594.3A 2015-04-24 2016-04-15 Procédé pour contrôler l'amortissement de la phase d'appui d'une prothèse du genou Active EP3285697B1 (fr)

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DE102015106392.1A DE102015106392B4 (de) 2015-04-24 2015-04-24 Verfahren zur Steuerung der Standphasendämpfung eines künstlichen Kniegelenks
PCT/EP2016/058394 WO2016169853A1 (fr) 2015-04-24 2016-04-15 Procédé pour contrôler l'amortissement de la phase d'appui d'une prothèse du genou

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EP (1) EP3285697B1 (fr)
JP (1) JP6751105B2 (fr)
CN (1) CN107530174B (fr)
CA (1) CA2983649C (fr)
DE (1) DE102015106392B4 (fr)
RU (1) RU2715683C2 (fr)
WO (1) WO2016169853A1 (fr)

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CN118615076A (zh) * 2024-08-15 2024-09-10 浙江强脑科技有限公司 假腿上楼梯控制方法、装置和存储介质

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Publication number Publication date
JP6751105B2 (ja) 2020-09-02
WO2016169853A1 (fr) 2016-10-27
US20210298921A1 (en) 2021-09-30
JP2018516635A (ja) 2018-06-28
EP3285697A1 (fr) 2018-02-28
CA2983649C (fr) 2023-09-26
RU2715683C2 (ru) 2020-03-02
US11963888B2 (en) 2024-04-23
RU2017140337A3 (fr) 2019-09-05
US11033406B2 (en) 2021-06-15
CN107530174B (zh) 2020-09-22
US20180085235A1 (en) 2018-03-29
CN107530174A (zh) 2018-01-02
DE102015106392B4 (de) 2020-07-09
DE102015106392A1 (de) 2016-10-27
CA2983649A1 (fr) 2016-10-27
RU2017140337A (ru) 2019-05-24

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